Flat panel detector based slot scanning configuration

ABSTRACT

The present invention relates to a diagnostic X-ray device, system or apparatus for performing diagnostic radiology and a method of configuring such a diagnostic X-ray device, system or apparatus. More specifically, the present invention relates to a diagnostic system for forming at least one image of an object having enhanced contrast. The system comprises a beam source adapted to produce an imaging beam and a masking member adapted to form at least one beam portion from the imaging beam and adapted to image the object. The system further comprises a flat panel detector positioned in a path of at least one beam portion penetrating the object and adapted to form at least one image of the object.

FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

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MICROFICHE/COPYRIGHT REFERENCE

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BACKGROUND OF THE INVENTION

This application is directed in general to diagnostic radiology using anX-ray device, system or apparatus. This application is directed inparticular to an X-ray device, system or apparatus using a flat paneldetector in a slot scanning configuration.

It is known that scattered X-rays have contrast reducing effects. One ofthe most significant challenges in using standard flat panel imaging isthat, after performing X-ray imaging of an object (a patient forexample), the X-ray image is composed of more scattered X-rays thandirect transmitted X-rays, thus reducing contrast. This is especiallytrue for thick objects (i.e., heavy patients).

Efforts have been made to improve contrast in diagnostic image radiologysystems, including using air gaps, improved electronics and certainforms of scanning techniques. However, such known techniques havegenerally proved to be unsatisfactory in obtaining high image qualitywhile maintaining rapid scanning rates and low exposure times. While itis possible to obtain images of good quality with very slow scanningspeeds, as with a single scanning beam for example, such low speedscanning techniques are not practical in diagnostic radiology in view ofthe fact that the patients' body parts and organs move while thepatients are being X-rayed. For example, it should be appreciated thatthe abdomen is the most difficult portion of the body to accuratelyX-ray in view of its relatively dense concentration of organs, bones andbody fluids.

Thus, if relatively long exposure times are required to obtain an X-rayimage, the images may be blurred due to the movement of the organs andbody parts being X-rayed and are useless for diagnostic purposes. Onepossible solution is to use a post-patient collimator to reduce oreliminate scatter. One limitation associated with previously usedpost-patient collimators is that they do not totally reduce or eliminatescattered radiation and may block X-rays that have passed through thepatient, forming useful doses.

Other efforts have been made to reduce or eliminate X-ray scattering,including using different types of slot scanners (pre-patient slotscanners for example) with an image detector, where the radiation isblocked prior to passing through the patient. In such manner, only slotsof radiation are passed through to impinge on the patient. The detectorand pre-patient collimator are swept across the patient, the images arecollected and pasted together to form a single image. It is contemplatedthat this type of slot scanner configuration may result in a 4-10x dosereduction. Increasing the slots reduces the total scan time.

One example of a previous effort to reduce or eliminate X-ray scatteringis disclosed in U.S. Pat. No. 4,096,391 (the '409 patent), incorporatedherein by reference in its entirety, which discloses a slot scannerconfiguration using film (a film cassette for example). The '409 patentdiscloses a multiple slot scanning method and apparatus. A conventionalX-ray tube projects a continuous X-ray beam in the direction of apatient. As described, a fore slot plate is positioned in the path ofthe X-ray beam at a predetermined position above the patient. The foreslot plate includes a plurality of narrow slots which permit the passageof a group of narrow parallel beam segments for scanning the patient.

Upon striking the patient, the narrow beam segments are partiallydefused or scattered in any a number of arbitrary directions. Thesescattered beam portions carry no significant information, and thus tendto blur or reduce the contrast in any resulting X-ray image. On theother hand, portions of the beam segments or portions penetrate directlythrough the patient. It is these penetrating beam portions which carryinformation as to the structural configuration of the patient's internalorgans.

In the abdominal area for example, extremely clear, high quality X-rayimages are necessary to obtain the degree of detail required to permitaccurate diagnosis of disease or the detection of tumors and otherimproper growths. However, due to the thickness, dense concentration ofmaterial in the abdomen, and the large radiation field necessary toimage the abdominal area, a large amount of X-ray scattering is created,thus making it difficult to obtain clear radiographic images of theabdomen, as mentioned previously. Accordingly, it is highly desirableand important to the advancement of abdominal diagnostic radiography forexample, that clearer X-ray images of this area of the body be obtained.

It should be appreciated that such previously used slot scanners orpre-patient collimators have limitations. They require a fixed source toimage distance (“SID”) (i.e., tube to detector). The materials used todetect the X-rays in the such previous designs (single crystal Si and Xegas for example) do not work effectively for high kV imaging used forcertain applications (radiography of R&F for example). Finally, themechanical scanning used to form the image makes high frame rate imagingsuch as fluoro imaging difficult if not impossible.

One other known attempt to reduce or eliminate X-ray scattering includesusing a slot scanner based on Xenon gas and avalanche detection. Stillanother attempt includes using a slot scanner based on single crystal Sisensors turned orthogonally to the X-ray incidence. While it isappreciated that both attempts may reduce X-ray scatter (due to the slotscanning) and photon counting, such attempts are generally only valid asscanned slot scanners.

BRIEF SUMMARY OF THE INVENTION

One embodiment relates in general to a diagnostic X-ray device, systemor apparatus for performing diagnostic radiology and a method ofconfiguring such a diagnostic X-ray device, system or apparatus. Morespecifically, one embodiment relates to a diagnostic system for formingat least one image of an object having enhanced contrast. The systemcomprises a beam source adapted to produce an imaging beam and a maskingmember adapted to form at least one beam portion from the imaging beamand adapted to image the object. The system further comprises a flatpanel detector positioned in a path of at least one beam portionpenetrating the object and adapted to form at least one image of theobject.

In at least one embodiment, the masking member comprises at least one ormore of a removable pre-patient collimator having at least one slotpositioned in a path of the imaging beam; a post-patient collimatorhaving at least one slot positioned in the path of the at least one beamportion penetrating the object and an X-ray collimator defining at leastone slot therein.

Embodiments of the system comprise an X-ray system and the imaging beamcomprises an X-ray beam. The system may have a table for supporting theobject and a support adapted to maintain a ratio of the source topre-patient collimator/source to constant image. Still other embodimentsof the system comprise the flat panel detector which is adapted tomeasure scatter, provide for interconnections or measure scatter andprovide for interconnections.

Yet another embodiment comprises a method of configuring a diagnosticsystem for forming at least one image of an object having enhancingcontrast. In this embodiment, the method comprises configuring ascanning portion and a flat panel detector. Configuring the scanningportion comprises configuring for at least one of high frame rateimaging and low dose scanning imaging. Configuring the flat paneldetector portion comprises configuring for at least one of standardscintillation, direct conversion and a hybrid of scintillation anddirect conversion. This method comprises performing a scan of an objectand forming an image using the configured system.

Still another embodiment comprises forming an image of an object usingan X-ray device. This embodiment comprises producing an X-ray beam usinga conventional X-ray source and creating a plurality of beam segmentsfrom the X-ray beam. The method further comprises scanning the objectusing at least one of the beam portion and producing an X-ray image on aflat panel detector. This method may comprises at least one of using aremovable pre-patient collimator to form the plurality of beam portionsand using a post-patient collimator passing at least one of the beamportion. Further, the method may comprise minimizing acquisition time.

BRIEF DESCRIPTION OF SEVERAL VIEWS OF THE DRAWINGS

FIG. 1 depicts a schematic illustration of a diagnostic radiological(X-ray) device, system or apparatus in accordance with certainembodiments of the present invention.

FIG. 2 depicts a schematic illustration of a diagnostic radiological(X-ray) device, system or apparatus (similar to that of FIG. 1)including a plan view of the pre-patient collimator and flat paneldetector in accordance with certain embodiments of the presentinvention.

FIG. 3 depicts a schematic illustration of a diagnostic radiological(X-ray) device, system or apparatus (similar to that of FIG. 1)including a post-patent collimator in accordance with certainembodiments of the present invention.

FIG. 4 depicts a schematic illustration of a diagnostic radiological(X-ray) device, system or apparatus (similar to that in FIG. 3)including a plan view of the post-patient collimator and flat paneldetector in accordance with certain embodiment of the present invention.

FIG. 5 depicts a partial side elevational view of a diagnosticradiological (X-ray) device, system or apparatus (similar to that inFIG. 3) including a side view of the pre- and post-patient collimatorsand flat panel detector in accordance with certain embodiments of thepresent invention.

FIG. 6 depicts a scintillator or direct conversion flat panel detectorhaving all lines active in accordance with certain embodiments of thepresent invention.

FIG. 7 depicts a flat panel detector having active lines separated atthe frequency of the pre-patient collimator in accordance with certainembodiments of the present invention.

FIG. 8 depicts a hybrid flat panel detector having direct conversion inone or more areas and scintillator rows in one or more areas inaccordance with certain embodiments of the present invention.

FIG. 9 depicts a detailed high level flow diagram depicting a method ofconfiguring a diagnostic radiology (X-ray) device, system or apparatusand forming at least one image using such configured system inaccordance with certain embodiments of the present invention.

FIGS. 10A and 10B depict a detailed flow diagram depicting a method ofconfiguring a diagnostic radiology (X-ray) device, system or apparatusand forming at least one image using such configured system inaccordance with certain embodiments of the present invention.

The foregoing summary, as well as the following detailed description ofcertain embodiments of the present invention, will be better understoodwhen read in conjunction with the appended drawings. For the purpose ofillustrating the invention, certain embodiments are shown in thedrawings. It should be understood, however, that the present inventionis not limited to the arrangements and instrumentality shown in theattached drawings.

DETAILED DESCRIPTION OF THE INVENTION

Clear, high quality X-ray images are necessary to obtain the degree ofdetail needed to permit accurate diagnosis of disease and detection oftumors and other improper growths in the crowded abdominal area, forexample. However, due to the thickness and dense concentration ofmaterial in the abdomen, and the large radiation field necessary toimage that area, a large amount of X-rays are scattered, thus making itdifficult to obtain clear images, as provided previously. Accordingly,it is highly desirable and important to the advancement of diagnosticradiography (abdominal diagnostic radiography for example) that clearX-ray images (i.e., having enhanced contrast) be obtained.

At least one embodiment relates in general to configuring a diagnosticX-ray device, system or apparatus and performing diagnostic radiologyusing such a configured X-ray device, system or apparatus. Moreparticularly, embodiments are directed to an X-ray device, system orapparatus having at least one of a standard X-ray collimator, aremovable pre-patient slot collimator, a post-patient collimator and aflat panel detector. One embodiment is adapted to perform either highframe rate imaging (fluoro and tomo imaging for example) or low dosescreening applications. Further, embodiments of the apparatus areadapted to obtain the benefits of low dose slot scanning for high KVapplications (“RAD”). For the purpose of illustration only, thefollowing detailed description references certain embodiments of anX-ray device, apparatus or system. However, it is understood that theembodiments may be used with other devices, apparatus or imagingsystems.

In at least one embodiment, a pre-patient slot collimator is positionedin the device, system or apparatus such that the system is employed as aslot scanner. Further, the pre-patient collimator may be removable, suchthat the system may be used in slot scanner or full field of view(alternatively referred to as “FOV”) modes. The slot scanner modeprovides dose reduction benefits, while the full FOV mode provides fastimage acquisitions (fluoro, tomo, cine, etc.). The flat panel detectormay be a scintillator detector or direct conversion detector, the shadedareas of the detector behind the pre-patient collimator may be used asdead space for interconnections or as active pixels to measure scatter,or a hybrid thereof. In at least one embodiment, the post-patientcollimator may be optimized to reject scatter between active pixel runs,but detect scatter in the shadowed pixels, enabling measurement of thescattered image. In at least one embodiment, the SID of thisconfiguration may be modified as long as the ratio of source topre-patient collimator/source to image remains constant. A mechanizedsupport may be used to maintain the ratio as the SID is changed.

Referring now to the drawings, wherein like reference numerals designateidentical or corresponding parts throughout the several views, and moreparticularly to FIG. 1 hereof, embodiments of the scanning apparatus andmethod are illustrated in schematic form. In at least one embodiment,the X-ray device, system or apparatus, generally designated 10,comprises at least one scanning and flat panel detector portions.

FIG. 1 depicts a conventional X-ray source 12 having a focal spot asindicated projecting an X-ray beam 14 (a continuous X-ray beam forexample) in the direction of an object 16. Currently available X-raysources have a focal spot size of about 2.0 millimeters or less (0.3millimeters for example). It will be understood that the object beingX-rayed may alternatively be referred to as a patient in view of thefact that at least one embodiment is viewed as being most beneficial indiagnostic radiology, although it should be appreciated that theembodiments may be used in radiographic studies of many different typesof animate and inanimate objects in addition to human patients.

According to at least one embodiment, a first or removable maskingmember 18 (a pre-patient slot collimator for example) is positioned inthe path of the X-ray beam 14 at a predetermined position above thepatient 16. In at least one embodiment, the pre-patient slot 18 isformed of a material, or combination of materials, generally opaque toX-ray beams (lead, steel and tungsten for example) and includes at leasttwo, but generally a plurality, of narrow slots 40 which permit thepassage of at least two, but generally a plurality of, narrow beamsegments or portions 42 for scanning the patient 16. It is contemplatedthat slots 40 may have a minimum dimension of at least two times (2×)the focal spot size of the conventional X-ray source 12 for example,although other dimensions and shapes are contemplated. It iscontemplated that the masking member may further comprise a conventionalfield limiting diaphragm or standard X-ray collimator (best viewed inFIG. 4) positioned above, below or in place of the pre-patientcollimator 18, limiting the total area of irradiation.

Upon striking the patient 16, the one or more narrow beam segments orportions 42 are partially defused or scattered in any number ofarbitrary directions (See FIG. 5 for example). These scattered beamportions carry no significant information, and thus tend to blur, reduceor otherwise affect the contrast in any resulting X-ray image. On theother hand, at least one but generally two or more of the beam segmentsor portions 42 penetrate directly through the patient 16. It is thesepenetrating beam segments or portions (alternatively referred to as“primary radiation”) which carry the information regarding thestructural configuration of the patient's internal organs.

Referring again to FIG. 1, patient 16 is shown supported by a table 20,which in at least one embodiment is constructed of an X-ray transparentmaterial, with the flat panel detector 22 positioned beneath the table20. A processor 26 (which is one embodiment, may include a control forX-ray source 12) is illustrated communicating with at least the flatpanel detector 22. The processor 26 is adapted to receive, store andprocess the image having significantly enhanced contrast and clarityrelative to previous known embodiments. In at least one embodiment, theapparatus 10 includes a video processor 28 and display 30, adapted todisplay the image having improved contrast and clarity (in real time forexample). While the processor 26, video processor 28 and display 30 areshown communicating via a hardwired connection, other methods ofcommunicating (wireless connections for example) are contemplated.

In operation, at least the pre-patient collimator 18 is moveable (usingany suitable drive device), scanning a patient 16 using at least one butgenerally a plurality of beam segments or portions 42. In this manner,the flat panel detector 22 is scanned by those beam segments or portions42 that penetrate the patient 22, resulting in a clear image which doesnot include any shadows or evidence of the existence of the pre-patientcollimator 18. More importantly, the use of at least the pre-patientcollimator 18 effectively attenuates most if not all scatteredradiation, so that the image on the flat panel detector 22 hassignificantly improved contrast and clarity relative to images takenwithout using such a pre-patient collimator. While it is contemplatedthat, in at least one embodiment, the pre-patient collimator 18 movesalone or synchronously with the flat panel detector, in otherembodiments, it is contemplated that the patient 16 and table 18 maymove with respect to the pre-patient collimator 18 and the flat paneldetector 22.

In at least one embodiment, the system 10 may include an arm or supportpivoted about an axis which passes through the focal spot of the X-raysource 12. The re-patient collimator 40 maybe mounted to the supportusing a mounting means which may be formed integral with the support. Inat least one embodiment, a post-patient collimator may be coupled to abase portion of the support (using pegs for example).

Linear motion of at least the pre- and/or post-patient collimator may beassured using a linear guide, for example to which the collimators arecoupled by means of conventional roller bearings or other suitablecoupling means which permit free linear motion with a minimum offriction. A conventional drive device (an electric motor for example)may be used to drive the support and pre- and post-patient collimatorsthrough a conventional worm gear drive for example. The worm gear driveincludes a worm gear driven by the motor and engaging a gear segment.The worm gear drive and electric motor assembly are entirelyconventional. The worm gear and electric drive assembly are suitable foruse with the embodiments of present invention in view of the fact thatthe worm gear arrangement enables precision motion while electric poweris normally conventionally available to energize the motor.

It is contemplated that many other types of drives and power sources,including hydraulic and belt arrangements may be used to power thesystem. Different types of drives may easily be adapted to the describedsystem in view of the present teachings by those skilled in the art.

It is further contemplated that a switch may be used to energize themotor. When energized, the motor drives the support through the wormgear drive, causing the pre- and/or post-patient slot collimators tomove. A start sensor, which may be a conventional limit switch, aphotocell device, or any similar type of conventional device, may beused to detect movement of at least one of the collimators. The startsensor is coupled to an X-ray source control, which is in turn coupledto the X-ray source 12, for energizing source 12 when the start sensoris triggered. A conventional stop sensor, similar to the start sensor,may be coupled to the X-ray source control for shutting off the source12 after the pre- and/or post-patient slot collimators have movedsufficiently to complete its scanning movement.

FIG. 2 depicts a schematic illustration of a diagnostic radiological(X-ray) device, system or apparatus (similar to that of FIG. 1)including a plan view of the pre-patient collimator and flat panel inaccordance with certain embodiments of the present invention.

Similar to FIG. 1, the conventional X-ray source 12 having a focal spotas indicated, projects an X-ray beam 14 (a continuous X-ray beam forexample) in the direction of patient 16. According to at least oneembodiment of the present invention, the removable pre-patientcollimator 18 is positioned in the path of the X-ray beam 14 at apredetermined position above the patient 16 and adapted to form one ormore beam segments or portions 42 that penetrate the patient. The flatpanel detector 22 is adapted to be scanned by those portions 42 thatpenetrate the patient.

In one embodiment, the flat panel detector 22, similar to that depictedin FIG. 6, comprises at least a standard scintillator or directconversion flat panel detector having one or more active lines. In atleast one embodiment, one or more lines are adapted to detect directradiation, while the other data lines are adapted to measure scatter(perhaps for diffraction or scatter imaging).

FIG. 3 depicts a schematic illustration of a diagnostic radiological(X-ray) device, system or apparatus (similar to that of FIG. 1)including a post-patent collimator in accordance with certainembodiments of the present invention. FIG. 3 depicts a conventionalX-ray source 212 having a focal spot as indicated projecting an X-raybeam 214 (a continuous X-ray beam for example) in the direction of apatient 216. Currently available X-ray sources have a focal spot size ofabout 2.0 millimeters or less (0.3 millimeters for example).

According to at least one embodiment, a removable pre-patient collimator218 is positioned in the path of the X-ray beam 214 at a predeterminedposition above the patient 216. In at least one embodiment, a maskingmember (a removable pre-patient collimator for example) is formed of amaterial, or combination of materials, generally opaque to X-rays (lead,steel and tungsten for example) and includes at least two, but generallya plurality of, narrow slots 240 which permit the passage of at leasttwo, but generally a plurality, of narrow parallel beam segments orportions 242 for scanning the patient 216. It is contemplated that slots240 may have a minimum dimension of at least two times (2X) the focalspot size of the conventional X-ray source 212 although other dimensionsand shapes are contemplated. It is further contemplated that the maskingmember may further comprise a conventional field limiting diaphragm orstandard X-ray collimator positioned above, below or in place of thepre-patient collimator 218, limiting the total area of irradiation.

Upon striking the patient 216, the one or more narrow beam segments orportions 242 are partially defused or scattered in any number ofarbitrary directions (best view in FIG. 5). These scattered beamportions carry no significant information, and thus tend to blur, reduceor otherwise affect the contrast in any resulting X-ray image. On theother hand, at least one but generally two or more, of the beam segmentsor portions 242 penetrate directly through the patient 216. It is thesepenetrating beam segments or portions (i.e., primary radiation) whichcarry the information regarding the structural configuration of thepatient's internal organs.

Referring again to FIG. 3, patient 216 is shown supported by a table220, which in at least one embodiment is constructed of an X-raytransparent material. In at least one embodiment, the masking memberfurther comprises at least a post-patient collimator or aft slot plate224 positioned beneath table 220 and above flat panel detector 222. Inat least one embodiment, the post-patient collimator 224 is comprised ofany suitable X-ray opaque material (the same or different material asthe pre-patient collimator 218) and includes at least one, but generallya plurality of, slots 244 which permit the passage of at least one, butgenerally a plurality, of parallel beam segments for scanning.

As illustrated, the post-patient collimator 224 includes at least one,but generally a plurality, of slots 226 whose width is small incomparison to their depth and which are significantly wider than slots240 in the pre-patient collimator 218 so that they are of sufficientwidth to accommodate those beam segments 242 which penetrate the patient216. Both the pre-and post-patient collimators 218, 224 include anidentical number of slots and are essentially congruent, although thepost-patient collimator 224 is substantially expended in scale relativeto the pre-patient collimator 218. Comparative dimensions of the pre-and post-patient collimators 218, 224 will be set forth subsequently.

In operation, the pre- and post-patient collimators 218, 224 are movedsynchronously to effectively scan the patient 216 using various beamportions 242. In this manner, the flat panel detector 222 is scanned bythe one or more beam segments or portions penetrating the patient 216,resulting in a clear image which does not include any shadows orevidence of the existence of the two slot collimators 218, 224. Moreimportantly, the use of the collimators 218, 224 results in a veryeffective attenuation of virtually all scattered radiation so that theimage on the flat panel detector 222 has significantly improved contrastand clarity relative to images taken without the combined collimators218, 224.

A central processor 226 is illustrated communicating with at least theflat panel detector 222. The central processor 226 is adapted toreceive, store and process one or more images having significantlyimproved contrast and clarity relative to previous known embodiments. Inat least one embodiment, the system 210 includes a video processor 228and display 230, adapted to display the one or more images havingimproved contrast and clarity (in real time for example). While thecentral processor 226, video processor 228 and display 230 are showncommunicating via a hardwired connection, other methods of communicating(wireless connections for example) are contemplated.

FIG. 4 depicts a schematic illustration of a schematic illustration of adiagnostic radiological (X-ray) device, system or apparatus (similar tothat of FIG. 3) including a plan view of the post-patient collimator andflat panel detector in accordance with certain embodiment of the presentinvention.

Upon striking the patient 216, the one or more narrow beam segments orportions 242 are partially defused or scattered in a number of arbitrarydirections. These scattered beam portions carry no significantinformation, and thus tend to blur, reduce or otherwise affect thecontrast in any resulting X-ray image. On the other hand, portions ofthe beam segments 242 (i.e., primary radiation) penetrate directlythrough the patient 216, and it is these penetrating beam portions whichcarry the information regarding the structural configuration of thepatient's internal organs.

In at least one embodiment of the flat panel detector 222 of FIG. 4(similar to that of FIG. 7) comprises at least two active linesseparated at the frequency of the pre-patient collimator 240. The deadspace between the active lines may be used for interconnections andpackaging. This embodiment may be especially useful for detector rowscomprised of single crystal direct conversion material. In thisconfiguration, the areas between the primary detector rows may have oneor more active rows to measure scatter.

As mentioned previously, exposure time is an important factor inobtaining clear X-ray images since involuntary movements of organs andthe like can cause unacceptable image blurring if exposures are carriedout over long intervals. In general, for abdominal examinations, theexposure time should be limited to approximately ½ second. Embodimentseasily permit short scanning intervals of approximately ½ second orless.

FIG. 5 depicts a partial side elevational view of a diagnosticradiological (X-ray) device, system or apparatus 210 (similar to that ofFIG. 3) comprising at least one scanning and flat panel detectorportions. In at least one embodiment, the scanning portion comprises atleast one masking member, which may include at least one of a standardX-ray collimator, a pre-patient collimator and a post-patientcollimator.

In FIG. 5, the conventional X-ray source 212 projects a continuous X-raybeam 214 in the direction of patient 216. System 210 includes aremovable, pre-patient collimator 218 placed at predetermined positionabove patient 216. Pre-patient collimator 216 includes at least one butgenerally a plurality of narrow slots 240 which permit the passage of agroup of narrow parallel beam segments 242 for scanning the patient 216.A conventional field limiting diaphragm or X-ray collimator 215 ispositioned above or below the pre-patient collimator 218 to limit thetotal area of irradiation in accordance with known practice.

Upon striking the patient 216, the narrow beam segments 242 arepartially defused or scattered as indicated by a plurality of arrows 241pointing in a number of arbitrary directions. These scattered beamportions 241 carry no significant information, and thus tend to blur orreduce the contrast in any resulting X-ray image. On the other hand,portions of the beam segments 242 penetrate directly through the patient216, and it is these penetrating beam portions, known as primaryradiation 243, which carry the information as to the structuralconfiguration of the patient's internal organs.

Referring again to FIG. 5, the patient is shown supported by a table 220which is constructed of a relatively light, X-ray transparent material.Beneath the table 220 a post-patient collimator 224 is positioned abovethe flat panel detector 222. The post-patient collimator 224 includes aplurality of slots 226 whose width is small compared to their depth andwhich are wider than the slots 240 in the pre-patient collimator 218 sothat they are of sufficient width to accommodate the expanded beamsegments 22 which penetrate the patient 216. The slots 226 preferablyhave a depth to width ratio of at least four to one. In one embodiment,both the pre- and post-patient collimators 218, 224 include an identicalnumber of slots and are essentially congruent, although the post-patientcollimator 224 is substantially expended in scale relative to thepre-patient collimator 219.

In operation, the pre- and post-patient collimators 218, 224 are movedsynchronously to effectively cause a scanning of the patient 216 by thevarious beam segments 243. In this manner the flat panel detector 222 isscanned by at least one of the beam segments 243 penetrating the patient216, resulting in a clear image which does not include any shadows orevidence of the existence of the collimators. More importantly the useof collimators results in a very effective attenuation of virtually allscattered radiation so that the image on the flat panel detector has asignificantly improved contrast and clarity relative to images takenwithout the combined slit plate structure of the present invention.

Having described in detail embodiments of the present invention, onemethod of operation will now be summarized. A patient 216 is firstplaced in an appropriate position on the X-ray table 220. The system 210is then started by switching on the motor. The start sensor activatesthe X-ray tube control to turn on the X-ray source 212 when motion of atleast one of the pre- and post-patient collimator 218, 224 is detected.The stop sensor is subsequently activated by motion of at least one ofthe pre- and post-patient collimators 218, 224, whereupon the X-raysource 21 is shut off by the X-ray tube control. At least one of thepre- and post-patient collimators must move a minimum distance equal tothe width of one slot plus the width of one slot separation, that is, atotal distance of about 2.5 cm for example. Preferably, at least one ofthe pre- and post-patient collimators 218, 224 moves two or three timesthis distance (at least 5 cm for example) to assure a complete anduniform scanning of the patient 216. It is noted that at the minimumscanning speed of a 5 cm scan would be accomplished in about ½ secondfor example, the proper maximum exposure time for abdominal X-rays.

Additional improvements in image contrast may be obtained by increasingthe depth of the slots in one or both of the collimators, increasing theseparation between slots, having narrower slots or having a greaternumber of narrower slots spaced closer together. One or more embodimentsof the system may be produced using one or more (a plurality forexample) of square, rectangular, circular or other geometrically shapedapertures in place of the elongated slots in one or both of thecollimators as shown. That is, each slot, in effect, would be replacedby one or more squares, rectangles, circles or other geometrical shapesand the neighboring multiplicity of apertures would be shifted in such amanner, that when the system is scanned across the patient, a uniformradiation exposure to the flat panel detector would result. However,such a system requires greater precision in manufacturing, sinceregistration among the apertures is required in two dimensions.

As provided previously, at least one embodiment relates in general toconfiguring a diagnostic radiology X-ray device, system or apparatus(similar to one or more of those embodiments discussed previously)adapted to perform a diagnostic radiological scan, forming at least oneimage of an object having enhanced contrast. More particularly, one ormore embodiments are directed to an X-ray device, system or apparatushaving a flat panel detector portion (similar to the those providedpreviously) adapted to be configured as at least one of scintillator,direct configuration, or hybrid of the two. In at least one embodiment,one or more areas or portions of the flat panel detector (behind thepre-patient collimator for example and depicted as shaded areas in thefigures) may be used as dead space for interconnects or as active pixelsto measure scatter. Further, the removable post-patient collimator maybe optimized to reject scatter between active pixel runs, but allowscatter in the shadowed pixels, enabling measurement of scattered imagesbeam portions.

In at least one embodiment, a flat panel portion of the X-ray device,system or apparatus is configurable for at least one of standardscintillation, direct conversion and a hybrid of scintillation anddirect conversion. The flat panel portion may include a detectoranti-scatter grid adapted to reduce scatter and enhance contrast. Aconfiguring device (an FET switch and scanning architecture for example)enables using all the data line read electronics only for the data rowsexposed by the slot pre-patient collimator with selected channelsdedicated to measuring the scatter from the channels shadowed by thepre-patient collimator. The flat panel detector (a multiplexed readoutfor example) may be configured in various configurations. The flat panelmay be configured as a standard scintillator with all lines active andread as a standard flat panel. Alternatively, the flat panel detectormay be configured using a multiplexed flat panel with rows of singlecrystal direct conversion material behind the pre-patient slots. Such amultiplexed flat panel may be configured as a dedicated slot scannerconfiguration, but may also be able to operate as a photon counting,energy discriminating detector at high kVs. In this embodiment, one ormore of the direct conversion strips may be separated by a predetermineddistance to minimize scatter (where each strip may be several pixel rowswide), and a mixed panel with some standard scintillator and some directconversion rows.

At least one embodiment of the device, system or apparatus may include asource to image distance (alternatives SID) that may be modified. Inthis embodiment, as long as the ratio of source to pre-patientcollimator/source to image (alternatively SPC/SI) remains constant. Inat least one embodiment, a support (a mechanized support for example)may be used to maintain the SPC/SI as the SID is changed or modified.

At least one embodiment comprises a device, system or apparatusconfigured as a slot system where the SID is variable, but having atleast one of the focal spot, pre-patient grid, and detector remainfocused and aligned. This configuration may be achieved using a supportthat retains a constant ratio of SPC/SI as the SID is changed. Variousconfigurations are contemplated for scanning the beam and designing thecollimator slots. In at least one embodiment, at least one of the beamwidth, spacing and size of the slots could vary over the field of view,tailoring scatter contribution (customizing the IQ/Dose over the FOV).One or more slots could be holes (in any pattern) and motion could be in2D slots. For example, the slots could be concentric circles and thescanning mechanism is changing tube to detector distance (or fixed tubeto detector distance, but changing tube to patient distance).

In one embodiment, the flat panel detector portion, depicted in FIG. 6,comprises at least a standard scintillator or direct conversion flatpanel detector, generally designated 600, having lines 650. In thisembodiment, all lines 650 are active. In at least one embodiment, one ormore lines 652 are adapted to detect direct radiation, while the otherdata lines 654 are adapted to measure scatter (perhaps for diffractionor scatter imaging).

In at least one embodiment of the flat panel detector depicted in FIG.7, generally designated 700, comprises at least two active stripes 752separated at the frequency of the pre-patient collimator. These activestripes may contain one or more active lines of detector elements. Thedead space 764 between the active lines 754 may be used for connectionsand packaging. This embodiment may be especially useful for detectorrows comprised of single crystal direct conversion material. In thisconfiguration, the areas between the primary detector rows (i.e., deadspace 754) may have one or more active rows to measure scatter.

In one embodiment, the of the flat panel detector, depicted in FIG. 8and generally designated 800, is a hybrid configuration. In thisembodiment, direct conversion in the one or more primary areas 870, andone or more scintillator rows 872 in the areas between.

FIGS. 9, 10A and 10B depict flow diagrams illustrating methods ofconfiguring a diagnostic radiology (X-ray) device, system or apparatusand forming at least one image using such a configured system inaccordance with certain embodiments. One or more embodiments of themethod comprise configuring scanning and flat panel detector portions ofthe system. At least one of these embodiments, configuring the scanningportion of the system, comprises configuring the scanning portion for atleast one of high frame rate imaging and low dose imaging. As providedpreviously, configuring the scanning portion for high frame averagingcomprises employing at least the removable pre-patient slot collimator,such that the system is employed as a slot scanner, achieving dosereduction benefits. Configuring the scanning portion for low doseimaging comprises not employing the removable pre-patient slotcollimator, such that the system is employed in FOV mode, enabling fastimage acquisitions (fluoro, tomo, cine, etc.).

In at least one of these embodiments, configuring the flat paneldetector portion, comprises configuring the flat panel detector portionfor at least one of measuring scatter, providing for interconnectionsand packaging, and a hybrid of measuring scatter and providing forinterconnects. As provided previously, configuring the flat paneldetector portion to measure scatter comprises configuring the flat paneldetector as a standard scintillator or direct conversion flat panel,with all data lines active. One or more of the data lines would detectdirect radiation, one or more of the other data lines would be used tomeasure scatter (for diffraction or scatter imaging for example).Configuring the flat panel detector portion to provide forinterconnections and packaging comprises configuring the flat paneldetector having at least two active data lines separated at thefrequency of the pre-patient collimator. The dead space between theactive data lines may be used for interconnections and packaging. Thisconfiguration may comprise detector rows comprised of single crystaldirect conversion material. Further, in this configuration, the areasbetween the primary detector rows may have one or more active rows tomeasure scatter. Configuring the flat panel detector portion as a hybridconfiguration comprises configuring the flat panel having directconversion in the primary areas and scintillator rows in one or moreareas between such primary areas.

FIG. 9 depicts a detailed high level flow diagram depicting a method ofconfiguring a diagnostic radiology (X-ray) device, system or apparatusand forming at least one image using such configured system inaccordance with certain embodiments. The method illustrated in FIG. 9,generally designated 900, comprises determining to perform a scan, Block910. After determining to perform the scan, method 900 comprisesconfiguring scanning and flat panel detector portions of the system,Blocks 920 and 930 respectively. In at least one embodiment, configuringthe scanning portion of the apparatus, Block 920, comprises configuringthe scanning portion for at least one of high frame rate imaging and lowdose imaging. As provided previously, configuring the scanning portionfor high frame averaging comprises employing at least the removablepre-patient slot collimator, such that the system is employed as a slotscanner, achieving dose reduction benefits. Configuring the scanningportion for low dose imaging comprises not employing the removablepre-patient slot collimator, such that the system is employed in FOVmode, enabling fast image acquisitions (fluoro, tomo, cine, etc.).

In at least one embodiment, configuring the flat panel detector portion,Block 930, comprises configuring the flat panel detector portion for atleast one of standard scintillation, direct conversion and a hybrid ofscintillation and direct conversion. As provided previously, configuringthe flat panel detector portion as a standard scintillator comprisesconfiguring the flat panel detector having all data lines active. One ormore of the data lines may detect direct radiation, one or more of theother data lines may be used to measure scatter (perhaps for diffractionor scatter imaging). Configuring the flat panel detector portion toprovide for interconnections and packaging comprises configuring theflat panel detector having at least two active data lines separated atthe frequency of the pre-patient collimator. The dead space between theactive data lines may be used for interconnections and packaging. Thisconfiguration may comprise one or more detector rows (comprised ofsingle crystal direct conversion material for example). Further, in thisconfiguration, one or more of the areas between the primary detectorrows may have a few active rows to measure scatter. Configuring the flatpanel detector portion as a hybrid configuration, comprising configuringthe flat panel having direct conversion in one or more of the primaryareas, and scintillator rows in one or more of the areas between theprimary areas.

FIGS. 10A and 10B depict a detailed flow diagram depicting a method ofconfiguring diagnostic radiology (X-ray) device, system or apparatus andforming at least one image using such configured system in accordancewith certain embodiments. The method illustrated in FIGS. 10A and 10B,generally designated 1000, comprises deciding to perform a scan, Block1010. In at least one embodiment, method 1000 comprises determining iflow dose scanning is required, Diamond 1012. If low dose scanning isrequired, a removable pre-patient slot collimator is used or employed inthe system, Block 1018, such that the system is employed in FOV mode,enabling fast image acquisitions (fluoro, tomo, cine, etc.). If low dosescanning is not required, method 1000 comprises determining if highframe rate imaging is required, Diamond 1014. If high frame rate imagingis required, the removable pre-patient slot collimator is not used, notemployed or removed from the system, block 1016. As provided previously,configuring the scanning portion for high frame averaging provides dosereduction benefits.

At least one embodiment of method 1000 comprises determining ifadditional reduction in scatter is required, Diamond 1021. If additionalreduction in scatter is required, at least one post-patient collimatormay be used in the system, Block 1022. If additional reduction inscatter is not required, method 1000 comprises determining if detectingdirect radiation and measuring scatter is required, Diamond 1024. Ifdetecting direct radiation and measuring scatter is required, at leastone embodiment of the flat panel may be operated as a standardscintillator or direct conversion detector having all data lines active,Block 1026. As such, a portion of the data lines would detect directradiation, other data lines may be used to measure scatter (for example,for diffraction or scatter imaging).

It should be appreciated that configuring the flat panel detector asdirect conversion, having active lines separated at the frequency of thepre-patient collimator or as a hybrid, 1026, 1031, 1032 may occur duringdesign of the system. However, embodiments are contemplated in whichsuch configuration may be selectable during operation.

In at least one embodiment, method 1000 comprises determining if spaceis required in the flat panel detector for interconnections andpackaging, Diamond 1028. If such space is required, the flat paneldetector is configured having two or more active data lines separated atthe frequency of the pre-patient collimator, Block 1031. However, ifsuch space is not required, the flat panel detector may be configured asa hybrid, Block 1032, having direct conversion in the primary areas, andscintillator rows in the areas between. Method 1000 further comprisesperforming a scan, forming at least one image using the configuredsystem.

While the invention has been described with reference to certainembodiments, it will be understood by those skilled in the art thatvarious changes may be made and equivalents may be substituted withoutdeparting from the scope of the invention. In addition, manymodifications may be made to adapt a particular situation or material tothe teachings of the invention without departing from its scope.Therefore, it is intended that the invention not be limited to theparticular embodiment disclosed, but that the invention will include allembodiments falling within the scope of the appended claims.

1. A diagnostic system for forming at least one image of an objecthaving enhanced contrast, the system comprising: a beam source adaptedto produce an imaging beam; a masking member adapted to form at leastone beam portion from said imaging beam and adapted to image the object;and a flat panel detector positioned in a path of at least one beamportion penetrating the object and adapted to form at least one image ofthe object, wherein said flat panel detector comprises first and secondactive detection lines, said first active detection lines configured todetect direct radiation, and said second active detection linesconfigured to measure scatter.
 2. The system of claim 1 wherein saidmasking member comprises at least a removable pre-patient collimatorhaving at least one slot positioned in a path of said imaging beam. 3.The system of claim 1, wherein said masking member comprises at least apost-patient collimator having at least one slot positioned in said pathof said at least one beam portion penetrating the object.
 4. The systemof claim 1 wherein said masking member comprises removable pre-patientand post-patient collimators.
 5. The system of claim 1 wherein saidmasking member comprises at least an X-ray collimator defining at leastone slot therein.
 6. The system of claim I wherein said imaging beamcomprises an X-ray beam.
 7. The system of claim 1 comprising an X-raysystem.
 8. (canceled)
 9. The system of claim 1 having a support adaptedto maintain a constant ratio of the source to pre-patientcollimator/source to image.
 10. The system of claim 1 wherein said flatpanel detector is configured for standard scintillation.
 11. The systemof claim 1 wherein said flat panel detector portion is configured fordirect conversion.
 12. The system of claim 1 wherein said flat paneldetector is configured as a hybrid of scintillation and directconversion.
 13. A method of configuring a diagnostic system for formingat least one image of an object having enhancing contrast, the methodcomprising: selectively configuring a scanning portion between highframe rate imaging and low dose scanning imaging; and configuring a flatpanel detector portion for at least one of standard scintillation,direct conversion and a hybrid of scintillation and direct conversion.14. (canceled)
 15. The method of claim 13 comprising forming an imageusing the diagnostic system.
 16. A method of forming an image of anobject using an X-ray device comprising: producing an X-ray beam using aconventional X-ray source; creating a plurality of beam segments fromsaid X-ray beam; selecting between a scanning mode and a full field ofview mode, wherein the scanning mode comprises scanning the object usingat least one of said beam segments; producing an X-ray image on a flatpanel detector.
 17. The method of claim 16 comprising using a removablepre-patient collimator to form said plurality of beam portions.
 18. Themethod of claim 16 comprising using a post-patient collimator passing atleast one of said beam portion.
 19. The method of claim 16 comprisingminimizing acquisition time.
 20. The method of claim 13 comprisingdetermining if at least one of the high frame rate imaging and low dosescanning imaging is required.
 21. The system of claim 1, wherein saidflat panel detector further comprises dead space for interconnects. 22.The method of claim 13, further comprising selectively configuring theflat panel detector portion between standard scintillation, directconversion and a hybrid of scintillation and direction conversion.